US5442674A - Device and automatic method for the geometrical calibration of an X-ray imaging system - Google Patents

Device and automatic method for the geometrical calibration of an X-ray imaging system Download PDF

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US5442674A
US5442674A US08/186,385 US18638594A US5442674A US 5442674 A US5442674 A US 5442674A US 18638594 A US18638594 A US 18638594A US 5442674 A US5442674 A US 5442674A
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phantom
detector
tube
imaging system
calibration
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Catherine Picard
Anne Rougee
Yves Trousset
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GE Medical Systems SCS
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/58—Testing, adjusting or calibrating thereof
    • A61B6/582—Calibration
    • A61B6/583—Calibration using calibration phantoms
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/027—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis characterised by the use of a particular data acquisition trajectory, e.g. helical or spiral
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods
    • A61B2017/00681—Aspects not otherwise provided for
    • A61B2017/00707—Dummies, phantoms; Devices simulating patient or parts of patient
    • A61B2017/00712—Dummies, phantoms; Devices simulating patient or parts of patient simulating mathematical properties, e.g. for testing of positioning in the isocentre or focus

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  • the present invention relates to a device and to an automatic method for the geometrical calibration of an X-ray imaging system.
  • Systems of this type are used chiefly in the medical field in order to analyze internal structures of the human body, notably vascular structures.
  • the aim of the invention is to enable the use of the system, by means of its easy calibration, for the quantitative assessment and, qualitative assessment of the dimensions of the internal structres analyzed.
  • the invention relates essentially to systems using 2D radiation detectors, for example substantially plane radiation detectors.
  • the invention also pertains to a method of rotating systems of X-ray imaging.
  • the geometrical operation that plays a role in the production of the image is a conical projection of an analyzed 3D object on a 2D space which is that of the plane of projection corresponding to the plane of detection.
  • the geometrical parameters that completely describe the conical projection are nine in number. These nine parameters may be presented according to different types of parametrization.
  • three first parameters relate to the three coordinates of the X-ray source S in the referential system R of the 3D space in which the analyzed object is placed;
  • three other parameters relate to the three Euler's angles associated with the change of referential system between the referential system R of the 3D space of the object and a referential system R' related to the conical projection, i.e. a referential system formed by a 2D referential system of the plane of projection P and a third axis orthogonal to the plane of projection;
  • three last parameters relate to the three coordinates of an arbitrary point I of the plane of projection P (for example the center of the image in the referential system R).
  • the referential system R is then a cylindrical referential system.
  • Knowledge of all or a part of these parameters is very often useful in radiology, notably when a quantitative data element pertaining to a 3D object is estimated from a measurement made in a 2D projection or in several 2D projections of this object. Parameters of each viewpoint must then be known. A viewpoint pertains to the orientation of the system with respect to the object. For example, we may take the standard problem of the estimation of the section of a vessel from one or more 2D projections. Now, gaining access to these parameters directly, i.e. for example by making direct measurement, on the acquisition system, of the distance between the X-ray source and the detector, is impossible or implies an excessive degree of imprecision.
  • geometrical calibration of an imaging system denotes the operation that leads to precise indirect knowledge of the geometrical parameters that play a role in the production of an image.
  • the principle which is a classic one, is based on the use of a geometrical phantom that is known in the 3D space and whose 2D projection is acquired.
  • the sequence of the operations carried out to this end comprises the following steps:
  • a known object namely a calibration phantom having a certain number of characteristic points whose position in space is known by coordinates measured with respect to a referential system proper to this object;
  • the image of this phantom is acquired under the geometrical conditions of a viewpoint (or incidence) that is to be calibrated;
  • each characteristic point of the object is associated with its trace in the acquired image, namely the projection;
  • the present invention therefore proposes a device enabling an automatic calibration that can be applied to any system of 2D X-ray imaging and in particular to any system used for purposes of 3D reconstruction.
  • the device of the invention is such that the unequivocal recognition of correspondences between the beads and their traces is automatic. This is obtained by choosing a phantom in which the beads are distributed, step by step or by degrees, in a sequence such that altitudes of beads, measured along the rotational axis of the imaging system and, especially, an axis of the phantom, are monotonically increasing (or decreasing) with an order number of the beads in the sequence.
  • an object of the invention is to provide an X-ray imaging system with a 2D detector positioned so as to be facing an X-ray tube, this detector and this tube being capable, in certain cases, of rotating together about an axis, this X-ray imaging system comprising a geometrical calibration device provided with a phantom having known dimensions and with measuring means for deducing, from images of the phantom projected on the 2D detector, of the coefficients of calibration of this X-ray imaging system.
  • the phantom comprises a step-by step succession of cellular structures having different levels, namely higher or lower levels, of radiological absorption as compared with their environment, each cellular structure being automatically identifiable by an ordered characteristic for the identification of this cellular structure.
  • a rotating imaging system of this type is indeed capable of applying 1000 or more angular positions on one rotation. Calibrations for all the angular positions, even when they are done automatically, are too lengthy to be capable of being repeated periodically, every week or every month. In fact, one workday has to be set aside for this purpose.
  • the method of the invention seeks to resolve this other problem by making the assumption that, although the theoretical dimensions of construction of the imaging system cannot be considered to have been met in the real system, it can nevertheless be assumed that the imaging system undergoes perfect circular rotation or almost perfect circular rotation.
  • the idea of the method then is to seek the intrinsic parameters of the system: ultimately those parameters which, in addition, give the direction of its axis of rotation axis. From these intrinsic parameters, which can be known with very high precision, it is then possible to make a computation of calibration coefficients for each angular position. It is shown, for example, that about a hundred calibrations lead to very precise knowledge of these intrinsic parameters. With this knowledge, 900 other "calibrations" are computed. Then, a total of 1,000 calibrations are known, with only 100 having been measured. The gain in time is considerable.
  • Another object of the invention is to provide a method for the geometrical calibration of an X-ray imaging system with a 2D detector rotating about an axis, facing an X-ray tube, said method comprising the following steps:
  • a phantom of known dimensions is placed between the tube and the detector;
  • a measurement is made, for a rotational position of the tube/detector assembly with respect to the phantom, and in the radiological image of the phantom projected on the 2D detector, of the coordinates of image loci of characteristic points of the phantom;
  • a deducing is done, for this rotational position of the tube/detector assembly, and in a referential system associated with the position of the phantom, of the calibration coefficients pertaining to the respective positions of a focal spot of radiation from the X-ray tube and of the 2D detector;
  • the calibration coefficients relating to a certain number of rotational positions of the tube/detector assembly are processed for the extraction therefrom of the intrinsic parameters of the X-ray imaging system which are independent of the rotational position of the tube/detector assembly;
  • FIG. 1 shows an imaging system that can be used to implement the invention with the presentation of the different referential systems of acquisition
  • FIGS. 2a to 2d respectively show a view in profile and a front view of the phantom according to the invention, the trace of the beads in the projections and a detailed view of the positioning of the beads being shown by overlay;
  • FIG. 3 shows the placing of the phantom in the imaging system
  • FIGS. 4a and 4b show images in projection of a particular shape of the phantom after processing
  • FIGS. 5a through 5d show geometrical representations that enable a better understanding of the method.
  • FIG. 1 shows an imaging system that can be used to implement the invention.
  • This system has an X-ray tube 1 with a radiation focal point or spot S.
  • a radiation detector 2 for example of the luminance amplifier type used in radiology, is placed facing the tube 1.
  • a line normal to the detection plane P of the detector 2 passes substantially through the focal spot S and the center I of detector 2. This may be necessary for the formation of conventional images but is not directly related to the problem of calibration.
  • the system may rotate with a known type of mechanism (not shown) for tomodensitometers or with a bow, about an axis 3, which is herein shown vertically but is normally horizontal.
  • the system also comprises a processor 4 that subjects the electrical signals measured by the detector 2 to a processing operation contained in a program 2 stored in a program memory 6. Images, or statistical results got from these processing operations, may be displayed on a monitor 7.
  • the invention makes it possible to resolve the problem of the automatic recognition of the corresponding 2D/3D points by using, as a calibration phantom, a particularly well-suited phantom that is shown in FIGS. 2a to 2d and 3.
  • this phantom is a plexiglass cylinder used as a support for a series of small metal beads overlaid into the wall of the cylinder and positioned evenly in the form of a helix.
  • the beads all have an identical diameter, for example 1 mm, except the middle bead, which has a greater diameter than the others, for example 3 mm.
  • the parameters of the helix are roughly adapted to the image acquisition system so that its projection is as as great as possible on the detector while, at the same time, it remains contained in the image.
  • the helix pitch and the pitch for sampling the beads on the helix are chosen in such a way that a sufficient number of beads appears in the projection without superimposing.
  • the dimensions in FIGS. 2a-2d are given in millimeters.
  • the cylinder 8 is occluded on both sides by a lid 9 which ensures its rigidity.
  • the phantom 8 is adapted, for example, to an acquisition system constituted by an X-ray source and a round field detector with a diameter of 37 cm, located at a distance of about 135 cm from the focal spots, while the object is about 100 cm from the focal spot S.
  • acquisition system constituted by an X-ray source and a round field detector with a diameter of 37 cm, located at a distance of about 135 cm from the focal spots, while the object is about 100 cm from the focal spot S.
  • the phantom 8 has a sufficient number of beads for the calibration. They are well distributed in the 3D space. Their projections are also well distributed in the plane P (which is the indispensable condition for a 3D calibration). However, the evenness of the distribution is not essential. To this end, the beads can easily be numbered as a function of their dimension along the Z axis. This is obtained here according to a very simple formula:
  • n bead number.
  • the phantom is positioned judiciously before the X-ray detector, i.e. essentially in such a way that the Z axis is roughly parallel to the plane P of the detector 2, and if the conicity of the beam is not too great, this order relation is also found in the 2D projections.
  • V the axis in the projection plane P that corresponds to the projection of the Z axis.
  • V axis coincides substantially with the vertical axis in the images of projection, i.e. that it is parallel to the columns of the image. If this is not so, a rotation may be introduced into the projection plane to arrive at this condition.
  • the referential system in the 3D space is defined as being related to the helix, i.e. the Z axis of the helix defines one of the axes of the referential system R, the other two axes being perpendicular to Z.
  • the coordinates of the beads are expressed very easily. This means that, once the calibration is done, the system has a vertical axis which is the one that was occupied by the axis of the phantom during the calibration. 3D reconstructions pertaining to different calibrations are therefore not directly comparable. This will be possible, on the contrary, with the method of the invention seen further below.
  • FIG 3 shows the phantom 8 positioned between the X-ray source S and the X-ray detector D.
  • the phantom is positioned in such a way that its main axis, the Z axis, is roughly parallel to the plane P, and in such a way that it is projected along the V axis of the detector.
  • the numbering of the beads can be done in an absolute way. Even if the top and the bottom of the projection of the helix are truncated (i.e. neither the first bead nor the last bead of the phantom is seen), we have an absolute reference which is the special, large, middle bead.
  • the special bead, or two special beads, or others, are preferably placed in the phantom at a place which will, in all likelihood, be in the field: in the middle of the phantom.
  • the phantom must have cellular structures, beads to simplify the description, that are visible in X-rays, and are well distributed in the 3D space. Their radiological contrast in relation to their environment needs to be high.
  • the projections of the beads must be contained in the 3D image at least for the central beads. It is not at all necessary for the support of the beads to be a hollow plexiglass cylinder.
  • This reference bead may be distinguished by a factor other than its diameter, for example its shape, its opacity to X-rays, its absence or again an unevenness in the distribution pitch or any other criterion.
  • the beads are distributed on a "degenerate" helix which is borne by a plexiglass sphere instead of being borne by a cylinder.
  • the reasoning shall be based on the preferred "helical” phantom as described here above. The entire method explained here below can also be applied with another method meeting the criteria.
  • the phantom 8 described here above is positioned in such a way that its main axis (Z axis) is somewhat parallel to the plane of the detector. This is the case, for example, when it is positioned so as to be laid on an examination table of an angiographic system, and when the bow that bears the X-ray tube and the detector is positioned in a plane perpendicular to the table. In this position, the projections of the beads verify the above order relation.
  • a digitized projection of the phantom is acquired under the conditions of incidence that are to be calibrated
  • the image is transferred to the image processor 4;
  • the image is corrected for possible geometrical distortions, for example with a method such as the one described in the French patent application No. 2 633 793 filed on 1st Jul. 1988;
  • the corrected image I is then subjected to an algorithm for the detection, localization and automatic labelling of the beads described hereinafter;
  • the image I is segmented.
  • the aim here is to eliminate from the image I, the signal of the projection of the plexiglass cylinder that supports the beads.
  • tools of mathematical morphology are used such as a top-hat transformation with a round-shaped structuring element having a size greater than the size of the beads in the image I.
  • a signal S1 is obtained, containing nothing more than the signal corresponding to the absorption of the beads.
  • the tools of mathematical morphology are of a known type and have been published in many works.
  • the image S1 needs to be rid of residual artefacts coming from the edges of the cylinder. To this end, once again, a transformation of mathematical morphology is used, aimed at eliminating the vertical structures in the image.
  • the resulting image is an image S2 that can be seen in FIG. 4b in negative.
  • the image S2 therefore contains all the beads (positive signal) on a background with zero value, apart from the noise.
  • the image S2 is then segmented.
  • the aim here is to keep only the signal coming from the large central bead of the phantom.
  • All of the beads in the image S2 are then detected. It is sought here to localize the projections of all the beads in the image to the nearest pixel.
  • the operation starts with the line 0 of the image (at the top of the detector). The entire image is crossed from the top to the bottom. A positive signal encountered in the image is declared to be a bead if this signal is above a certain threshold 1. The number 0 is given to the first bead encountered, then the number is incremented at each bead encountered, until the bottom of the image. It is certain that the order of the numbers is the right one, owing to the properties of the helix described here above.
  • the aim here is to know the coordinates of each of the beads in the image, with sub-pixel precision.
  • a computation is made of the center of gravity in terms of gray levels of the set of pixels around the detected bead, such that their gray level is higher than a second threshold, threshold T2 (threshold T2 ⁇ threshold T1).
  • threshold T2 threshold T2 (threshold T2 ⁇ threshold T1).
  • a computation of this type is undertaken, for example, in the second French patent application referred to here above. Its principle is based on the fact that the beads are fine enough so as not to absorb all of the X-radiation. Then, when there is no absorption saturation, a pixel is obtained.
  • the large bead is then detected in the image S3; its coordinates are then known to the nearest pixel. Its coordinates are compared with those of all the beads detected in the image S2 and thus, in the list of all the beads, the largest bead is recognized.
  • the proposed parameter estimation algorithm uses the conjugate gradient minimization technique applied to the mean square error criterion.
  • This standard technique necessitates the computation of the criterion and of its prime derivatives as a function of the parameters.
  • This algorithm has been published by W. H. Press, B. P. Flannery, S. A. Teukolsky and W. T. Vetterling in Numerical Recipes in C, Cambridge University Press, 1988, ch. 10.6, pp. 317 & ff.
  • Other algorithms called Simplex and Newton and described in the same pages in this work, could also be used.
  • Simplex has the advantage of being adaptable to any coherent system of parametrization. However, it does not converge rapidly.
  • the algorithm of the conjugate gradient converges more quickly but calls for a choice of parametrization such that the analytic expressions of the parameters are derivable. This is the case with the parametrization described here above.
  • the computations pertaining to this algorithm have been presented to the Congress on "3D Advanced Imaging Processing In Medecine", Rennes, France during the 14th annual IEEE EMBS annual conference from 2 to 4 Nov. 1992 by Anne Rougee, Catherine Picard, Cyril Ponchut and Yves Trousset.
  • Standardization around this initial value, it is possible to compute the value of a criterion corresponding to a shift by one unit on each axis of the space of the parameters, and then to carry out a change of variable in this space by changing the scale on each axis so that any shift by one unit on each axis prompts the same effect on the criterion.
  • 3D reconstruction machine is applied to a machine that carries out radiographies of an object at different angles of incidence obtained by rotation about an axis. These radiographies are then used to reconstruct 3D information.
  • This machine can be built, for example, on the basis of a rigid ring on which the tube/detector assembly rotates, in which case the rotational axis is fixed and never changes in the course of time. Or else, it may built as a structure based on a tilting stand that supports the tube/detector assembly, in which case the axis of rotation may be positioned in different ways in space.
  • the following procedure may be used: an estimation is made of the parameters of the conical projection, view by view, during a first step and then the intrinsic parameters are estimated on the basis of these parameters during a second step.
  • the method of automatic calibration is particularly well suited to estimating the calibration coefficients, view by view, in the course of a rotation.
  • the helix is positioned on the examination table with its Z axis approximately centered on the rotational axis of the machine. For each of the viewpoints of acquisition of a machine during a rotation, the projection of the helix will be obtained, and thus all the acquired images will be processed, with the method described here above.
  • the proposed parametrization (with cylindrical 3D coordinates) is suited to estimating the parameters along a circular trajectory about the Z axis.
  • the initialization and standardization steps are carried out for the first view only.
  • the values of the parameters found for the first view are then used to initialize the estimation of the parameters of the next view, and so on and so forth, until the last view. This enables the computations to be accelerated.
  • geometrical parameters for each viewpoint are obtained. These geometrical parameters are stored in the digital disk of the machine, and will be used in every 3D reconstruction step.
  • the geometry of acquisition of the 3D reconstruction machine can parametrized with a far larger number of parameters which are, preferably:
  • the N points I n (n-1, N) forming the trajectory of I are considered.
  • this trajectory is plane and orthogonal to Z'.
  • the closest plane, in terms of the least squares, to the set of points I n is sought, and the direction of Z', which is the normal to this plane, is deduced therefrom.
  • (X n Y n Z n ) be the coordinates of a point I n .
  • the coefficients (a,b,c) that minimize the distance d(a,b,c) are sought.
  • the isocenter is the center of both the trajectory of I and the trajectory of S. This center will therefore be sought by analyzing the trajectory of I.
  • a plane is defined as being orthogonal to Z' and as having one dimension along Z' equal to the mean of the dimensions of the points I n . All the points I n are projected orthogonally to this plane at points I n . Since the trajectory of I is assumed to be circular, the points I' n are located, in principle, on a circle. Then the circle that is closest, in terms of the least squares, to the set of the points I' n is sought, which gives us:
  • the coordinates of the isocenter which is herein defined as the intersection of ⁇ and of the rotational axis (it is the center of the circle that was found).
  • C(A,r) be a circle with a center A and a radius r. What must be done is to define a distance d(A,r) between the circle C(A,r) and the set of points I' n .
  • any method of minimization is used to seek the parameters A and r of the circle (or, in the method 2, the parameters a, r and ⁇ 0 ) which minimize the distance to the circle. Once these parameters are found, the procedure is over since:
  • the radius of the trajectory of J is known: it is r;
  • the center of the trajectory of S is known since, by definition, it is the same as that of the trajectory of I which has just been found in the previous step.
  • the radius can now be sought
  • the points S' n which are projections of the points s on the plane ⁇ are considered.
  • the radius of the trajectory of S is defined as the mean of the distances between the isocenter O and the points S' n :
  • the operation uses the projections I' and S' n in the plane ⁇ . For each n, the polar angles (with respect to 0) of I 'n and S 'n are computed and their difference (see FIG. 5d) is called ⁇ n . ⁇ is estimated as being the mean of the values ⁇ n .
  • the other two axes of this referential system are fixed, except for one rotation.
  • the first view is assigned an angle ⁇ 0 related to a preferred position of the machine.
  • these coordinates depend only on the two angles ⁇ 1 and ⁇ 2 .
  • ⁇ 1n and ⁇ 2n are computed.
  • ⁇ 1 is defined as the mean of the values of ⁇ 1n and the same is done for ⁇ 2n .
  • Another possible method would consist of making a direct estimation of the global parameters of the machine on the basis of all the coordinates of the beads detected in all the projections of the helix.
  • this method is a lengthy one.

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CN111449668A (zh) * 2020-04-23 2020-07-28 深圳市安健科技股份有限公司 三维扫描重建中实时几何校正的标记装置、方法及系统
US12306361B2 (en) 2021-09-09 2025-05-20 Canon Medical Systems Corporation X-ray diagnostic apparatus and medical image processing apparatus
EP4252695A1 (fr) 2022-03-29 2023-10-04 Ecential Robotics Procédé d'enregistrement d'une image médicale en 3d à l'aide d'un fantôme d'enregistrement
WO2023186996A1 (fr) 2022-03-29 2023-10-05 Ecential Robotics Procédé d'enregistrement d'une image médicale 3d avec un fantôme d'enregistrement
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DE102022212466B3 (de) 2022-11-22 2024-02-29 GOEKELER Messtechnik GmbH Kalibriernormal für einen industriellen Computertomographen

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